WO1998056447A1 - Catheter ayant une flexibilite modulable et son procede de fabrication - Google Patents

Catheter ayant une flexibilite modulable et son procede de fabrication Download PDF

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Publication number
WO1998056447A1
WO1998056447A1 PCT/US1998/011788 US9811788W WO9856447A1 WO 1998056447 A1 WO1998056447 A1 WO 1998056447A1 US 9811788 W US9811788 W US 9811788W WO 9856447 A1 WO9856447 A1 WO 9856447A1
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WO
WIPO (PCT)
Prior art keywords
tubular member
stiffhess
outer tubular
distal end
flow rate
Prior art date
Application number
PCT/US1998/011788
Other languages
English (en)
Other versions
WO1998056447A9 (fr
Inventor
Henry J. Pepin
Original Assignee
Scimed Life Systems, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Scimed Life Systems, Inc. filed Critical Scimed Life Systems, Inc.
Priority to EP98926403A priority Critical patent/EP1009468B1/fr
Priority to DE69840385T priority patent/DE69840385D1/de
Priority to CA002290996A priority patent/CA2290996C/fr
Priority to JP50301599A priority patent/JP4074918B2/ja
Publication of WO1998056447A1 publication Critical patent/WO1998056447A1/fr
Publication of WO1998056447A9 publication Critical patent/WO1998056447A9/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0009—Making of catheters or other medical or surgical tubes
    • A61M25/0012—Making of catheters or other medical or surgical tubes with embedded structures, e.g. coils, braids, meshes, strands or radiopaque coils
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0009—Making of catheters or other medical or surgical tubes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M25/00—Catheters; Hollow probes
    • A61M25/0043—Catheters; Hollow probes characterised by structural features
    • A61M25/0054—Catheters; Hollow probes characterised by structural features with regions for increasing flexibility
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
    • B29C48/15—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor incorporating preformed parts or layers, e.g. extrusion moulding around inserts
    • B29C48/151—Coating hollow articles
    • B29C48/152—Coating hollow articles the inner surfaces thereof
    • B29C48/153—Coating both inner and outer surfaces
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
    • B29C48/25—Component parts, details or accessories; Auxiliary operations
    • B29C48/30—Extrusion nozzles or dies
    • B29C48/32—Extrusion nozzles or dies with annular openings, e.g. for forming tubular articles
    • B29C48/34—Cross-head annular extrusion nozzles, i.e. for simultaneously receiving moulding material and the preform to be coated
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C70/00—Shaping composites, i.e. plastics material comprising reinforcements, fillers or preformed parts, e.g. inserts
    • B29C70/04—Shaping composites, i.e. plastics material comprising reinforcements, fillers or preformed parts, e.g. inserts comprising reinforcements only, e.g. self-reinforcing plastics
    • B29C70/28—Shaping operations therefor
    • B29C70/40—Shaping or impregnating by compression not applied
    • B29C70/50—Shaping or impregnating by compression not applied for producing articles of indefinite length, e.g. prepregs, sheet moulding compounds [SMC] or cross moulding compounds [XMC]
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
    • B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
    • B29C48/00—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor
    • B29C48/03—Extrusion moulding, i.e. expressing the moulding material through a die or nozzle which imparts the desired form; Apparatus therefor characterised by the shape of the extruded material at extrusion
    • B29C48/09—Articles with cross-sections having partially or fully enclosed cavities, e.g. pipes or channels

Definitions

  • This invention relates to the field of intravascular medical devices, and more particularly, to the field of catheters such as angiographic and guide catheters used for the placement of medicines and medical devices within the body.
  • the invention is directed to an improved guide or diagnostic catheter incorporating an annealed proximal zone having lower flexibility than a distal zone, wherein a transition zone provides varying flexibility between the annealed proximal zone and the distal zone for improved catheter performance.
  • Angiographic and guide catheters are well known in the field of medicine for use in conjunction with other catheters for the treatment of cardiovascular disease through such procedures as percutaneous transluminal coronary angioplasty (PTCA) procedures.
  • Guide catheters aid in treatment of arterial lesions by providing a conduit for positioning dilatation balloon systems across an arterial stenosis.
  • the need for a greater variety of guide catheters to treat different types of circumstances has grown tremendously as the techniques for the use of such devices has grown.
  • the catheter During the treatment of cardiovascular disease, the catheter must be able to traverse tortuous pathways through blood vessels in a manner that mimmizes trauma. In order for the physician to place the catheter at the correct location in the vessel, the physician must apply longitudinal and rotational forces.
  • the catheter must be stiff enough to resist the formation of kinks, while at the same time, the catheter must possess flexibility to be responsive to maneuvering forces when guiding the catheter through the vascular system.
  • the catheter must be rigid enough to push through the blood vessel, but yet flexible enough to navigate the bends in the blood vessel.
  • the guide or angiographic catheter must exhibit good torque control such that manipulation of a proximal portion of the catheter is responsively translated to the tip or distal end of the catheter to curve and guide the catheter through the tortuous pathways.
  • the catheter must have torsional rigidity to transmit the applied torque.
  • a support member is added to the shaft.
  • This support member is often comprised of a metal braid or a coil embedded in the shaft.
  • the catheter is guided through the aorta over the aortic arch and down to the ostium of the vessel which is to be treated. It is preferable to have a soft tip or flexible section engage the ostium. Therefore, it is advantageous to have the proximal section more rigid to transmit the forces applied, but have the distal end more flexible to allow for better placement of the catheter. Having the distal section more flexible also creates a less traumatic section to contact the blood vessel.
  • catheters are often manufactured using polymers in conjunction with the above-mentioned support member using a metal braid or coil, wherein the support member is incorporated into the tube of the guide catheter.
  • Catheters can be formed of three layers.
  • An inner tubular member is used which defines an inner lumen which may be formed of a material that decreases the coefficient of friction such as that encountered between a balloon catheter and the inner lumen of the catheter.
  • the support member conforms to the outside of the inner layer and is often comprised of a metal braid or coil.
  • the third outer tube is commonly formed from a polymer and overlays the support member.
  • a catheter In order to meet the above requirements of rigidity and flexibility, a catheter is desired which has regions of varying stiffness which may be readily changed during manufacturing to meet the need for the greater variety of devices necessary to treat different types of circumstances.
  • Catheters may be manufactured using this approach, but its practical application may be limited to joining two materials to form two zones of flexibility with a transition therebetween. Thus, with this approach, additional manufacturing steps are necessary to provide for additional regions. These regions of varying stiffness are necessary to provide rigidity to push the catheter through the blood vessel, flexibility to navigate the bends in the blood vessel, and torsional stiffness to correctly place the catheter by maintaining torque control without excessive energy storage which can cause undesirable movement of the catheter end.
  • the present invention overcomes many of the disadvantages found in the prior art by providing a guiding catheter and method of manufacture for use in coronary angioplasty and other cardiovascular interventions which incorporates an annealed low flexibility proximal zone, wherein a transition zone separates the proximal zone and a high flexibility distal zone.
  • the catheter is subjected to a slicking operation as described herein to improve the smoothness and increase the flexibility of the high flexibility distal zone in order to better traverse the aortic arch shape, while reducing excess energy storage.
  • At least a portion of the proximal zone is subsequently annealed to provide a high level of stiffness for optimal support and pushability.
  • a guide or angiographic catheter comprising an inner tubular member having a proximal end, a distal end, and a lumen therethrough.
  • a braid member overlies and conforms to the inner tubular member, and has a distal end terminating proximate the distal end of the inner tubular member.
  • the catheter is further comprised of a first outer tubular member and a second outer tubular member.
  • the first outer tubular member substantially overlies the braid member and is comprised of a first material, and has a proximal end terminating proximate the proximal end of the inner tubular member.
  • the first outer tubular member has a first stiffhess over a region extending distally a predefined distance from the proximal end, and a second stiffness extending distally beyond the predefined distance.
  • the first outer tubular member is annealed over the predefined distance to increase the stiffhess of the first outer tubular member over the predefined distance from a second stiffhess to a first stiffhess to increase the rigidity and pushability of the catheter.
  • the second outer tubular member overlies the braid member and is comprised of a second material having a third stiffness, wherein the third stiffhess is less than the second stiffness.
  • the second outer tubular member has a distal end terminating proximate the distal end of the inner tubular member.
  • the first outer tubular member joins the second outer tubular member in a transition region defined by gradual transition from the first material of the first outer tubular member to the second material of a second outer tubular member to form a region of continuous differential stiffhess from a second stiffhess of the first outer tubular member to the third stiffhess of the second outer tubular member.
  • the length of the transition region is a transition distance and may be controlled to determine the length of the region of differential stiffhess.
  • the first material adheres to the second material and forms transition region, wherein the amount of the material of the second tubular member relative to the amount of the material of the first tubular member increases distally through the transition zone.
  • first tubular member and the second outer tubular member form an outer tubular member coextensive with the inner tubular member.
  • the first outer tubular member in the preferred embodiment is extruded from a polyether block amide polymer (PEBA), commercially available under the tradename PEBAX.
  • PEBAX polyether block amide polymer
  • the first outer tubular member is formed from PEBAX having a 72 D durometer rating.
  • the second outer tubular member is formed from PEBAX having a 40 D durometer rating.
  • a first outer longitudinal surface of the first outer tubular member and a second outer longitudinal surface of the second outer tubular member are "slicked" to provide a smooth first outer longitudinal surface and second outer longitudinal surface for improved flexibility to navigate the bends in the blood vessel and to improve torque control to correctly place the catheter without excessive energy storage.
  • the catheter of a preferred embodiment may further comprise a tip member which is butt- welded to the distal end of the inner tubular member and to the distal end of the second outer tubular member.
  • the tip member is preferably formed of urethane.
  • a method of manufacture is provided for forming a tubular assembly for use in a catheter. The method includes the step of providing an inner tubular member having a proximal end, a distal end, and a lumen therethrough. The method provides a braided metallic member having a proximal end, a distal end, and a lumen therethrough. The braided metallic member is preferably sleeved or braided over the inner tubular member so that the braided member has a distal end terminating proximate the distal end of the inner tubular member.
  • an extrusion head having a proximal end and a distal end and a first extrusion port and a second extrusion port, where the extrusion head includes a tubular portion between the proximal end and the distal end which has a lumen therethrough.
  • the first extrusion port and the second extrusion port are in fluid communication with the tubular portion at the distal end of the extrusion head so that a material may be applied to the tubular portion.
  • the method includes a step of applying a second material at a first flow rate through the first extrusion port while passing the braid covered inner tubular member for a second distance through the extrusion head in a proximal direction beginning at the distal end of the inner tubular member, where the second material has the third stiffhess and forms a second outer tubular member overlying the braid member.
  • the method provides a step of applying a first material through the second extrusion port while continuing to pass the braid covered inner tubular member through the extrusion head in a proximal direction beyond the second distance, where the first material is applied at a flow rate which is gradually increased within the transition distance to a second flow rate.
  • the first material has the second stiffness which is greater than the third stiffhess and forms the first outer tubular member overlying the braid member.
  • the flow rate of the second material is gradually decreased from the first flow rate by an amount proportional to the increase of the flow rate of the first material so that the first material gradually displaces the second material within the transition region. This occurs until the second material has a zero flow rate and the first material has a second flow rate.
  • the flow rate of the first material is maintained at the second flow rate beyond the transition region until the desired length of tubing is passed through the extrusion head.
  • the method next includes the step of slicking a portion of the first outer longitudinal surface and the second outer longitudinal surface for a predetermined slicking time and a predetermined slicking temperature to provide additional surface smoothness.
  • the method then provides the step of annealing the first outer tubular member over a region extending distally a predefined distance from the proximal end of the first outer tubular member to increase the stiffhess of the first outer tubular member over the predefined distance to a first stiffhess, wherein the first stiffhess is greater than the second stiffhess.
  • the method next provides the step of butt welding a tip having a lumen to the distal end of the inner tubular member and the distal end of the outer tubular member.
  • FIG. 1 is a perspective view of a catheter showing a preferred embodiment of the present invention
  • Fig. 2 is a plan view showing a portion of the catheter;
  • Fig. 3 is a cross section view of Fig. 2 taken along line 3-3;
  • Fig. 4 is a cross section of the guide catheter of Fig. 2 taken along the longitudinal axis to show the construction of the first outer tubular member and the second outer tubular member;
  • Fig. 5 is a flow chart of a process used to manufacture the first outer tubular member and the second outer tubular member elements of the catheter.
  • Fig. 6 is a cross section of an extrusion head for the process of Fig. 5 to illustrate the first extrusion port and the second extrusion port used in application of material to manufacture the first outer tubular member and the second outer tubular member.
  • Fig. 1 is a perspective view of a catheter showing a preferred embodiment of the present invention.
  • Fig. 1 shows a catheter 10 which comprises an outer tubular member 12, a tip member 14, and a hub 16.
  • Outer tubular member 12 substantially overlies a braid member 18, and braid member 18 overlies an inner tubular member 20 (see, Fig. 4).
  • Hub 16 is attached to an outer surface of outer tubular member 12.
  • Outer tubular member 12 has a proximal end 22 and a distal end 24.
  • Braid member 18 has a distal end 26 which terminates proximate distal end 24 of outer tubular member 12.
  • Inner tubular member 20 has a proximal end 28 and a distal end 30, wherein proximal end 28 and distal end 30 terminate proximate the proximal end 22 and the distal end 24 of outer tubular member 12, respectively.
  • Inner tubular member 20 has a lumen 32 extending from proximal end 28 to distal end 30. Access to lumen 32 is provided via proximal end 34 of hub 16.
  • Tip member 14 has proximal end 36, distal end 38 and a lumen 40 extending 5 from proximal end 36 to distal end 38. Tip member 14 is attached at proximal end 36 to distal end 24 of outer tubular member 12 and distal end 30 of inner tubular member 20 such that lumen 32 of inner tubular member 20 and lumen 40 of tip member 14 form a continuous lumen extending from proximal end 28 of inner tubular member 20 through distal end 38 of tip member 14.
  • Fig. 2 is a plan view showing a portion of the catheter 10.
  • First outer tubular member 42 terminates proximally at proximal end 22.
  • Second outer tubular member 44 terminates distally at distal end 24.
  • First outer tubular member 42 has a first outer longitudinal surface 43, and second outer tubular member 44 has a 5 second outer longitudinal surface 45.
  • First outer tubular member 42 may be manufactured from a polymeric material.
  • first outer tubular member 42 and second outer tubular member 44 are extruded from a polyether block amide polymer (PEBA), commercially available under the tradename PEBAX.
  • PEBA polyether block amide polymer
  • first outer tubular member 42 is extruded from PEBAX having 0 a 72 D durometer rating and second outer tubular member 44 is extruded from PEBAX having a 40 D durometer rating.
  • first outer longitudinal surface 43 and second outer longitudinal surface 45 are "slicked" to provide additional surface smoothness.
  • Tip member 14 in a preferred embodiment, is formed of urethane and is butt 5 welded to distal end 24 of outer tubular member 12 and distal end 30 of inner tubular member 20.
  • First outer tubular member 42 joins second outer tubular member 44 in a transition region defined by a transition distance 46, wherein a gradual transition occurs from the first material of first outer tubular member 42 to the second material of second outer tubular member 44 which forms a region of continuous differential stiffhess from the second stiffness of first outer tubular member 42 to the third stiffhess of second outer tubular member 44.
  • the second stiffhess is greater than the third stiffness.
  • the continuous differential stiffhess of the transition region defined by transition distance 46 may be controlled by controlling the length of the gradual transition from the first material of first outer tubular member 42 to the second material of second outer tubular member 44. In a preferred embodiment, the transition distance is between 1.5 inches to 5 inches.
  • a second distance 48 is defined between the transition region and distal end 24 of second outer tubular member 44, and is a region having a third stiffhess. In a preferred embodiment, second distance 48 is 0.5 inches. In a preferred embodiment, the length of tip member 14 is 0.06 inches.
  • First distance 50 is defined as the distance between proximal end 28 of first outer tubular member 42 and the proximal end of the transition region. Initially, first distance 50 defines the portion of first outer tubular member 42 which has a second stiffness. In a preferred embodiment, a portion of first outer tubular member 42 is annealed over a predefined distance 52, which extends distally from proximal end 28 of first outer tubular member 42 and is less than first distance 50. The annealing process increases the stiffhess of first outer tubular member 42 within predefined distance 52 from the second stiffhess to a first stiffhess. In a preferred embodiment, the first stiffhess is greater than the second stiffhess.
  • the predefined distance 52 is preferably about 26 inches.
  • Fig. 3 is a cross-sectional view of Fig. 2 taken along line 3-3.
  • Fig. 3 shows inner tubular member 20 which is preferably manufactured from PEBAX having a 67D-72D stiffhess.
  • Inner tubular member 20 has lumen 32 therethrough and braid member 18 conforming to an outer longitudinal surface 54 of inner tubular member 20.
  • First outer tubular member 42 overlies braid member 18.
  • Fig. 4 is a cross-section of the catheter of Fig. 2 taken along the longitudinal axis to show the construction of the first outer tubular member and the second outer tubular member.
  • Fig. 4 shows braid member 18 overlying inner tubular member 20.
  • First outer tubular member 42 substantially overlies braid member 18 and second outer tubular member 44 overlies braid member 18.
  • First outer tubular member 42 and second outer tubular member 44 are joined within the transition region defined by transition distance 46 which is the gradual transition from the first material 56 of first outer tubular member 42 to second material 58 of second outer tubular member 44.
  • Transition distance 46 forms of a region of continuous differential stiffhess from the second stiffhess of first material 56 to the third stiffhess of second tubular member 44.
  • first material 56 adheres to second material 58 forming a combination of both materials with relative amounts of each material varying distally through the transition zone.
  • the varying concentrations are shown as a wedge shape 60.
  • first outer tubular member 44 and the second outer tubular member 46 form outer tubular member 12, which extends between proximal end 22 and distal end 24, and which is equivalent to the distance between proximal end 28 and distal end 30 of inner tubular member 20.
  • Fig. 4 shows tip member 14 being attached at proximal end 36 to distal end 24 of second outer tubular member 44 and distal end 30 of inner tubular member 20 so that lumen 32 of inner tubular member 20 and lumen 40 of tip member 14 form a continuous lumen extending from proximal end 28 of inner tubular member 20 through distal end 38 of tip member 14.
  • Fig. 5 is an illustration of a process used to manufacture the first outer tubular member and the second outer tubular member elements of the catheter.
  • Fig. 5 shows extrusion head 70.
  • Extrusion head 70 is comprised of a first extrusion port 72 illustrated by arrow 74 and a second extrusion port 76 illustrated by arrow 78.
  • First material 56 is shown as "material A”
  • second material 58 is shown as "material B”.
  • Inner tubular member 20 with braided overlay 18 are passed through extrusion head 70. Entry of first material 56 to extrusion head 70 is provided via arrow 78 at a second flow rate.
  • Second material 58 is provided to extrusion head 70 via arrow 74 at a first flow rate.
  • the combination of braid member 18 and inner tubular member 20 are thus passed through extrusion head 70 in the direction shown by arrow 84 to extrude first outer tubular member 42 and second outer tubular member 44.
  • Fig. 6 is a cross section of the extrusion head 70 of Fig. 5 to illustrate the first extrusion port 72 and the second extrusion port 76 used in application of material to extrude the first outer tubular member 42 and the second outer tubular member 44.
  • Fig. 6 shows extrusion head 70 having tubular portion 80 and lumen 82.
  • First extrusion port 72 and second extrusion port 76 provide entry of second material 58 and first material 56, respectively, to lumen 82 of tubular portion 80 adjacent distal end 86 of extrusion head 70.
  • the combination of braided metallic member 18 and inner tubular member 20 are shown as partially constructed catheter 88 being passed through lumen 82.
  • Partially constructed catheter 88 is passed through lumen 82 in a direction from proximal end 90 of extrusion head 70 to distal end 86 of extrusion head 70.
  • Partially constructed catheter 88 may be assembled by sleeving braid member 18 over inner tubular member 20 such that braid member 18 has distal end 26 terminating proximate distal end 30 of inner tubular member 20.
  • the second material 58 is first applied at a first flow rate through first extrusion port 72 while partially constructed catheter 88 is continually passed or tracked through lumen 82 of extrusion head 70 for a second distance 48 beginning at distal end 30 of inner tubular member 20 to form the second outer tubular member 44 which overlies braid member 18.
  • a first material 56 is applied through second extrusion port 76 while tracking extrusion head 70 in a proximal direction beyond second distance 48 where the first material 56 is applied at a flow rate which is gradually increased to a second flow rate within transition distance 46.
  • the flow rate of second material 58 is gradually decreased from the first flow rate by an amount proportional to the increase of the flow rate of first material 56.
  • First material 56 gradually displaces second material 58 until second material 58 has a zero flow rate and first material 56 has the second flow rate.
  • Transition distance 46 is defined as the transition region wherein the gradual transition from second material 58 of second outer tubular member 44 to first material 56 of first outer tubular member 42 occurs to form a region of continuous differential stiffhess between the third stiffness of the region of second distance 48 and the second stiffness of first distance 50 outside of predefined distance 52.
  • transition distance 46 may be selected to control the transition region of continuous differential stiffhess from the third stiffness of second outer tubular member 44 to the second stiffhess of first outer tubular member 42.
  • first outer tubular member 42 and second outer tubular member 44 form outer tubular member 12 which is coextensive with inner tubular member 20.
  • the transition structure illustrated as 60 is formed by second material 58 being applied through inner radial port 92 and collecting within cavity 94, while being deposited upon partially constructed catheter 88.
  • first material 56 pushes out through outer radial port 96 into second material 58 within cavity 94. Outside of transition distance 46 the flow rate of first material 56 is maintained at the second flow rate for a length of first distance 50 until distal end 86 of extrusion head 70 reaches proximal end 28 of inner tubular member 20.
  • first outer longitudinal surface 43 and second outer longitudinal surface 45 is slicked for a predetermined slicking time and a predetermined slicking temperature to provide additional smoothness.
  • the predetermined temperature is being between 400°F and 450°F degrees, and is preferably 415°F degrees.
  • the entire surface of first outer longitudinal surface 43 and second outer longitudinal surface 45 is slicked by passing the tubular member through a heated die.
  • the first outer tubular member 42 is then annealed over a region extending distally the predefined distance 52 from proximal end 22 of first outer tubular member 42 for a predetermined time at a predetermined temperature.
  • the annealing process increases the stiffhess of first outer tubular member 42 along predefined distance 52 from a second stiffhess to a first stiffhess.
  • the predetermined time is 15 minutes and the predetermined temperature is 315°.
  • the predefined distance is 26 inches.
  • tip member 14 is butt welded to distal end 30 of inner tubular member 20 and to distal end 24 of second outer tubular member 44 such that lumen 32 of inner tubular member 20 and lumen 40 of tip member 14 form a continuous lumen extending from proximal end 28 of inner tubular member 20 through distal end 38 of tip member 14.

Abstract

L'invention concerne un cathéter de guidage ou un cathéter pour angiographie et un procédé de fabrication à utiliser dans les interventions cardiovasculaires. Ledit cathéter comporte une zone proximale recuite à faible flexibilité, une zone de transition séparant la zone proximale et une zone distale de flexibilité élevée. Le cathéter est soumis à une opération de lissage qui permet d'améliorer la régularité de la zone distale à flexibilité élevée, ce afin d'assurer une meilleure traversée de l'arc de l'aorte et de réduire le stockage d'énergie excessif. Cette zone proximale est recuite de sorte qu'un niveau élevé de rigidité soit obtenu de manière qu'une caractérisque optimale de support et une capacité optimale à être poussé soient produites. Une zone médiane fait la transition entre la rigidité élevée de la zone proximale et la flexibilité élevée de la zone distale de sorte que le gondolage ou le tortillement soient éliminés.
PCT/US1998/011788 1997-06-09 1998-06-08 Catheter ayant une flexibilite modulable et son procede de fabrication WO1998056447A1 (fr)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP98926403A EP1009468B1 (fr) 1997-06-09 1998-06-08 Catheter ayant une flexibilite modulable et son procede de fabrication
DE69840385T DE69840385D1 (de) 1997-06-09 1998-06-08 Katheter mit kontrollierter flexibilität und verfahren zur herstellung
CA002290996A CA2290996C (fr) 1997-06-09 1998-06-08 Catheter ayant une flexibilite modulable et son procede de fabrication
JP50301599A JP4074918B2 (ja) 1997-06-09 1998-06-08 制御された柔軟性を有するカテーテル及び製造方法

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US08/873,142 US5938653A (en) 1997-06-09 1997-06-09 Catheter having controlled flexibility and method of manufacture
US873,142 1997-06-09

Publications (2)

Publication Number Publication Date
WO1998056447A1 true WO1998056447A1 (fr) 1998-12-17
WO1998056447A9 WO1998056447A9 (fr) 2000-08-24

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PCT/US1998/011788 WO1998056447A1 (fr) 1997-06-09 1998-06-08 Catheter ayant une flexibilite modulable et son procede de fabrication

Country Status (7)

Country Link
US (1) US5938653A (fr)
EP (1) EP1009468B1 (fr)
JP (1) JP4074918B2 (fr)
AT (1) ATE418353T1 (fr)
CA (1) CA2290996C (fr)
DE (1) DE69840385D1 (fr)
WO (1) WO1998056447A1 (fr)

Cited By (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2002102356A (ja) * 2000-08-02 2002-04-09 Cordis Corp 自己拡張型ステント用の供給装置
DE20110121U1 (de) * 2001-06-19 2002-12-05 Braun Melsungen Ag Katheter
EP1658950A1 (fr) * 2003-08-27 2006-05-24 Pla Giken Co., Ltd. Appareil de moulage par extrusion de tube multicouche en resine
EP1658951A1 (fr) * 2003-08-27 2006-05-24 Pla Giken Co., Ltd. Appareil de moulage par extrusion pour tube en resine
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US5938653A (en) 1999-08-17
JP4074918B2 (ja) 2008-04-16
JP2002506363A (ja) 2002-02-26
ATE418353T1 (de) 2009-01-15
CA2290996A1 (fr) 1998-12-17
EP1009468A1 (fr) 2000-06-21
EP1009468B1 (fr) 2008-12-24
DE69840385D1 (de) 2009-02-05
WO1998056447A9 (fr) 2000-08-24
CA2290996C (fr) 2007-07-10

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